US20100305464A1 - Neonatal colorimetric carbon dioxide detector - Google Patents
Neonatal colorimetric carbon dioxide detector Download PDFInfo
- Publication number
- US20100305464A1 US20100305464A1 US12/472,011 US47201109A US2010305464A1 US 20100305464 A1 US20100305464 A1 US 20100305464A1 US 47201109 A US47201109 A US 47201109A US 2010305464 A1 US2010305464 A1 US 2010305464A1
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- Prior art keywords
- calorimetric
- carbon dioxide
- neonatal
- orifice
- dioxide detector
- Prior art date
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- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 title claims abstract description 182
- 229910002092 carbon dioxide Inorganic materials 0.000 title claims abstract description 95
- 239000001569 carbon dioxide Substances 0.000 title claims abstract description 87
- 239000012528 membrane Substances 0.000 claims abstract description 45
- 230000029058 respiratory gaseous exchange Effects 0.000 claims abstract description 45
- 238000004891 communication Methods 0.000 claims abstract description 17
- 239000012530 fluid Substances 0.000 claims abstract description 16
- 208000018773 low birth weight Diseases 0.000 claims description 6
- 231100000533 low birth weight Toxicity 0.000 claims description 6
- 238000003780 insertion Methods 0.000 claims description 5
- 230000037431 insertion Effects 0.000 claims description 5
- 238000001514 detection method Methods 0.000 claims description 4
- 230000013011 mating Effects 0.000 claims 1
- 210000003437 trachea Anatomy 0.000 abstract description 3
- 239000000126 substance Substances 0.000 abstract description 2
- 239000007789 gas Substances 0.000 description 10
- 238000000034 method Methods 0.000 description 6
- 238000004519 manufacturing process Methods 0.000 description 5
- 239000000853 adhesive Substances 0.000 description 2
- 230000001070 adhesive effect Effects 0.000 description 2
- 230000003466 anti-cipated effect Effects 0.000 description 2
- 238000010276 construction Methods 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 239000011800 void material Substances 0.000 description 2
- 206010002091 Anaesthesia Diseases 0.000 description 1
- 241000219198 Brassica Species 0.000 description 1
- 235000003351 Brassica cretica Nutrition 0.000 description 1
- 235000003343 Brassica rupestris Nutrition 0.000 description 1
- 206010067508 Low birth weight baby Diseases 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 230000037005 anaesthesia Effects 0.000 description 1
- QKSKPIVNLNLAAV-UHFFFAOYSA-N bis(2-chloroethyl) sulfide Chemical compound ClCCSCCCl QKSKPIVNLNLAAV-UHFFFAOYSA-N 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000003238 esophagus Anatomy 0.000 description 1
- 238000001746 injection moulding Methods 0.000 description 1
- 235000010460 mustard Nutrition 0.000 description 1
- 230000000241 respiratory effect Effects 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
- 238000009423 ventilation Methods 0.000 description 1
- 238000003466 welding Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/083—Measuring rate of metabolism by using breath test, e.g. measuring rate of oxygen consumption
- A61B5/0836—Measuring rate of CO2 production
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2503/00—Evaluating a particular growth phase or type of persons or animals
- A61B2503/06—Children, e.g. for attention deficit diagnosis
Definitions
- the present invention relates in general to the field of calorimetric carbon dioxide detectors, particularly for use with low-birth weight neonatal patients.
- Airway adapters are generally used with patients being given respiratory assistance, such as patients under anesthesia, or patients on life support systems, to connect between the patient airway (mouth, nose, tracheal tube) and a ventilating tube of a breathing apparatus.
- the ventilating tubes convey breathing gases to the patient and exhaled breath away from the patient (typically, the airway adapter is in the form of a short connector of tubular shape making a connection between the generally different cross sections of tubes).
- End-tidal carbon dioxide (ETCO 2 ) detection provides a non-invasive indication of the proper insertion of the airway tube is obtained by the analysis of the exhaled breath gases. End-tidal carbon dioxide (ETCO 2 ) detection indicates to the clinician whether the airway tube is inserted correctly into the trachea. If inserted correctly, carbon dioxide is detected. If the airway tube is inserted incorrectly (into the esophagus), no carbon dioxide is detected and the clinician knows to remove the airway tube and reinsert it.
- Airway components are typically made as plastic injection moldings, keeping production costs low. The amount of void volume (also known as dead space) in such airway components is typically very considerable. For neonatal applications, especially those with low birth weight, the patient has very little exhalation air volume. Airway adapters needs to have minimal added void volume to reduce the effects of gas mixing which would adversely affect the integrity of a calorimetric carbon dioxide detector membrane.
- Existing devices claim to have 3 mL of internal volume (dead space), when in actuality, these devices have 5 mL of internal volume before they are inserted into a circuit and 3 mL of internal volume after inserted into a circuit.
- a neonatal calorimetric carbon dioxide detector has a calorimetric carbon dioxide detector membrane having a pH-sensitive chemical indicator that undergoes calorimetric change in the presence of carbon dioxide.
- the detector has a patient orifice in fluid communication with the baby's airway and a respiration equipment orifice connected to a breathing system.
- the patient orifice is connected to a breathing tube and when the breathing tube is inserted correctly into the trachea, as the baby exhales, carbon dioxide interacts with the calorimetric membrane which changes color based upon the concentration of carbon dioxide.
- the total internal volume of the neonatal calorimetric carbon dioxide detector is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- a neonatal calorimetric carbon dioxide detector including an enclosure having a patient orifice in fluid communication with a patient's airway and a respiration equipment orifice.
- the respiration equipment orifice is also in fluid communication with the patient orifice.
- a calorimetric membrane is held within the enclosure and visible from outside of the enclosure.
- the calorimetric membrane is situated such that exhalation gas from the patient orifice passes around and/or through the calorimetric membrane before leaving the respiration equipment orifice.
- the total internal volume of the enclosure is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- a neonatal calorimetric carbon dioxide detector including a patient orifice in fluid communication with a patient's airway and a respiration equipment orifice in fluid communication with the respiration equipment orifice.
- a bottom surface of the respiration equipment orifice is affixed to a top surface of the patient orifice.
- a calorimetric membrane is held between the respiration equipment orifice and the patient orifice. The calorimetric membrane is in fluid communication with the patient orifice such that exhalation gas from the patient orifice passes through and around the calorimetric membrane before leaving out of the respiration equipment orifice.
- the total internal volume of the respiration equipment orifice and the patient orifice is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- FIG. 1 illustrates a perspective view of a neonatal calorimetric carbon dioxide detector of the present invention.
- FIG. 2 illustrates a second perspective view of a neonatal calorimetric carbon dioxide detector of the present invention.
- FIG. 3 illustrates a plan view of the neonatal calorimetric carbon dioxide detector of the present invention before assembly.
- FIG. 4 illustrates a plan view of the neonatal calorimetric carbon dioxide detector of the present invention after assembly.
- FIG. 5 illustrates a cross-sectional view of the neonatal calorimetric carbon dioxide detector of the present invention.
- the present invention discloses a neonatal calorimetric carbon dioxide detector 10 suited for low birth weight neonatal patients (low birth weight babies are often classified as those who weigh less than 2.5 kg).
- FIGS. 1 and 2 top and bottom perspective views of a neonatal calorimetric carbon dioxide detector 10 of the present invention are shown. Although one specific method of fabrication and construction of the neonatal calorimetric carbon dioxide detector 10 is shown, many such methods and fabrication techniques are known and all are anticipated an included here within.
- FIGS. 1 and 2 includes a top molded section 14 , a bottom molded section 18 and a calorimetric membrane 16 .
- the top molded section 14 includes a respiration equipment orifice 12 for accepting air flow from a breathing device (e.g., a breathing bag or ventilation equipment, not shown).
- the bottom molded section 18 includes a patient orifice 19 for communicating with the patient.
- the top molded section 14 and the bottom molded section 18 form an enclosure 10 having a respiration equipment orifice 12 at the top and a patient orifice 19 at the opposite end.
- the calorimetric membrane 16 is held on one side above a perforated grill section 26 and kept in place by, for example, two molded protrusions 24 on the inside surface of the top molded section 14 . Although one specific method of fabrication and holding of the calorimetric membrane 16 in position while marrying the top molded section 14 to the bottom molded section 18 is shown, many such methods and fabrication techniques are known and all are anticipated an included here within.
- the calorimetric membrane 16 is situated in fluid communication with the air flow from the patient orifice 19 such that, as the patient exhales, the calorimetric membrane 16 is exposed to the exhaled gases as the exhaled gases pass around and/or through the calorimetric membrane 16 .
- the calorimetric membrane 16 will change color depending upon the presence and the concentration of the gas of interest (e.g., carbon dioxide). For example, one typical carbon dioxide calorimetric membrane 16 is blue when no CO 2 is present, green when 1% to 2% CO 2 is present, yellow/green when 2% to 5% CO 2 is present and yellow when more than 5% CO 2 is present. In another example, another typical carbon dioxide calorimetric membrane 16 is purple when less than 0.5% CO 2 is present, tan when 0.5% to 2% CO 2 is present, mustard yellow when 2% to 5% CO 2 is present and yellow when more than 5% CO 2 is present. To prevent exposure to the gas of interest before use, it is known to ship the neonatal calorimetric carbon dioxide detector 10 in a hermetically sealed container or bag.
- the gas of interest e.g., carbon dioxide
- the neonatal calorimetric carbon dioxide detector 10 is preferably made from a transparent or translucent material, making the calorimetric membrane 16 is visible from outside through a surface of the neonatal calorimetric carbon dioxide detector 10 .
- FIG. 3 a plan view of the neonatal calorimetric carbon dioxide detector 10 is shown before assembly. Shown, is the relationship of the top molded section 14 and the bottom molded section 18 with the calorimetric membrane 16 positioned to be held between the top molded section 14 and the bottom molded section 18 .
- There are many ways known to join the top molded section 14 and the bottom molded section 18 one of which is to have one or more pegs, posts or snaps 24 that fit into holes 20 , thereby holding the top molded section 14 and the bottom molded section 18 together with or without an adhesive. Other methods include the use of adhesives, ultrasonic welding, etc.
- FIG. 4 a plan view of the present invention after assembly is shown.
- the total internal air volume is approximately 3.8 mL or less than 3.8 mL. Insertion of the neonatal calorimetric carbon dioxide detector 10 into an airway circuit increases the total internal air volume 45 (see FIG. 5 ) by approximately 1 mL and preferably by less than 1 mL.
- FIG. 5 a cross-sectional view of the present invention after assembly is shown.
- the neonatal calorimetric carbon dioxide detector top molded section 14 interfaces to respiration equipment through, for example, a gas tube 60 .
- the bottom molded section 18 interfaces to the patient through, for example, a tracheal or endo-tracheal tube 50 .
- the total internal air volume is approximately 3.8 mL or less than 3.8 mL. Insertion of the neonatal calorimetric carbon dioxide detector 10 into an airway circuit increases the total internal air volume 45 by approximately 1 mL and preferably by less than 1 mL.
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- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
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Abstract
Description
- The present invention relates in general to the field of calorimetric carbon dioxide detectors, particularly for use with low-birth weight neonatal patients.
- Airway adapters are generally used with patients being given respiratory assistance, such as patients under anesthesia, or patients on life support systems, to connect between the patient airway (mouth, nose, tracheal tube) and a ventilating tube of a breathing apparatus. The ventilating tubes convey breathing gases to the patient and exhaled breath away from the patient (typically, the airway adapter is in the form of a short connector of tubular shape making a connection between the generally different cross sections of tubes).
- End-tidal carbon dioxide (ETCO2) detection provides a non-invasive indication of the proper insertion of the airway tube is obtained by the analysis of the exhaled breath gases. End-tidal carbon dioxide (ETCO2) detection indicates to the clinician whether the airway tube is inserted correctly into the trachea. If inserted correctly, carbon dioxide is detected. If the airway tube is inserted incorrectly (into the esophagus), no carbon dioxide is detected and the clinician knows to remove the airway tube and reinsert it.
- Airway components are typically made as plastic injection moldings, keeping production costs low. The amount of void volume (also known as dead space) in such airway components is typically very considerable. For neonatal applications, especially those with low birth weight, the patient has very little exhalation air volume. Airway adapters needs to have minimal added void volume to reduce the effects of gas mixing which would adversely affect the integrity of a calorimetric carbon dioxide detector membrane. Existing devices claim to have 3 mL of internal volume (dead space), when in actuality, these devices have 5 mL of internal volume before they are inserted into a circuit and 3 mL of internal volume after inserted into a circuit.
- There exists a serious need for a sampling airway adapter for use with low birth weight neonatal patients, which overcomes the disadvantages of available adapters by reducing the internal volume to approximately 1 mL when inserted into a circuit and used with neonatal patients.
- A neonatal calorimetric carbon dioxide detector has a calorimetric carbon dioxide detector membrane having a pH-sensitive chemical indicator that undergoes calorimetric change in the presence of carbon dioxide. The detector has a patient orifice in fluid communication with the baby's airway and a respiration equipment orifice connected to a breathing system. The patient orifice is connected to a breathing tube and when the breathing tube is inserted correctly into the trachea, as the baby exhales, carbon dioxide interacts with the calorimetric membrane which changes color based upon the concentration of carbon dioxide. The total internal volume of the neonatal calorimetric carbon dioxide detector is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- In one embodiment, a neonatal calorimetric carbon dioxide detector is disclosed including an enclosure having a patient orifice in fluid communication with a patient's airway and a respiration equipment orifice. The respiration equipment orifice is also in fluid communication with the patient orifice. A calorimetric membrane is held within the enclosure and visible from outside of the enclosure. The calorimetric membrane is situated such that exhalation gas from the patient orifice passes around and/or through the calorimetric membrane before leaving the respiration equipment orifice. The total internal volume of the enclosure is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- In another embodiment, a neonatal calorimetric carbon dioxide detector is disclosed including a patient orifice in fluid communication with a patient's airway and a respiration equipment orifice in fluid communication with the respiration equipment orifice. A bottom surface of the respiration equipment orifice is affixed to a top surface of the patient orifice. A calorimetric membrane is held between the respiration equipment orifice and the patient orifice. The calorimetric membrane is in fluid communication with the patient orifice such that exhalation gas from the patient orifice passes through and around the calorimetric membrane before leaving out of the respiration equipment orifice. For neonatal application in patients of low birth weight, The total internal volume of the respiration equipment orifice and the patient orifice is less than or equal to 3.8 mL before being attached to a breathing circuit and the neonatal calorimetric carbon dioxide detector adds less than or equal to 1 mL to a breathing circuit after being inserted.
- The invention can be best understood by those having ordinary skill in the art by reference to the following detailed description when considered in conjunction with the accompanying drawings in which:
-
FIG. 1 illustrates a perspective view of a neonatal calorimetric carbon dioxide detector of the present invention. -
FIG. 2 illustrates a second perspective view of a neonatal calorimetric carbon dioxide detector of the present invention. -
FIG. 3 illustrates a plan view of the neonatal calorimetric carbon dioxide detector of the present invention before assembly. -
FIG. 4 illustrates a plan view of the neonatal calorimetric carbon dioxide detector of the present invention after assembly. -
FIG. 5 illustrates a cross-sectional view of the neonatal calorimetric carbon dioxide detector of the present invention. - Reference will now be made in detail to the presently preferred embodiments of the invention, examples of which are illustrated in the accompanying drawings. Throughout the following detailed description, the same reference numerals refer to the same elements in all figures.
- The present invention discloses a neonatal calorimetric
carbon dioxide detector 10 suited for low birth weight neonatal patients (low birth weight babies are often classified as those who weigh less than 2.5 kg). - Referring to
FIGS. 1 and 2 , top and bottom perspective views of a neonatal calorimetriccarbon dioxide detector 10 of the present invention are shown. Although one specific method of fabrication and construction of the neonatal calorimetriccarbon dioxide detector 10 is shown, many such methods and fabrication techniques are known and all are anticipated an included here within. - The example of
FIGS. 1 and 2 includes a top moldedsection 14, a bottom moldedsection 18 and acalorimetric membrane 16. The top moldedsection 14 includes arespiration equipment orifice 12 for accepting air flow from a breathing device (e.g., a breathing bag or ventilation equipment, not shown). The bottom moldedsection 18 includes apatient orifice 19 for communicating with the patient. The top moldedsection 14 and the bottom moldedsection 18 form anenclosure 10 having arespiration equipment orifice 12 at the top and apatient orifice 19 at the opposite end. - The
calorimetric membrane 16 is held on one side above aperforated grill section 26 and kept in place by, for example, two moldedprotrusions 24 on the inside surface of the top moldedsection 14. Although one specific method of fabrication and holding of thecalorimetric membrane 16 in position while marrying the top moldedsection 14 to the bottom moldedsection 18 is shown, many such methods and fabrication techniques are known and all are anticipated an included here within. Thecalorimetric membrane 16 is situated in fluid communication with the air flow from thepatient orifice 19 such that, as the patient exhales, thecalorimetric membrane 16 is exposed to the exhaled gases as the exhaled gases pass around and/or through thecalorimetric membrane 16. Therefore, thecalorimetric membrane 16 will change color depending upon the presence and the concentration of the gas of interest (e.g., carbon dioxide). For example, one typical carbon dioxidecalorimetric membrane 16 is blue when no CO2 is present, green when 1% to 2% CO2 is present, yellow/green when 2% to 5% CO2 is present and yellow when more than 5% CO2 is present. In another example, another typical carbon dioxidecalorimetric membrane 16 is purple when less than 0.5% CO2 is present, tan when 0.5% to 2% CO2 is present, mustard yellow when 2% to 5% CO2 is present and yellow when more than 5% CO2 is present. To prevent exposure to the gas of interest before use, it is known to ship the neonatal calorimetriccarbon dioxide detector 10 in a hermetically sealed container or bag. - There are many ways known to join the top molded
section 14 and the bottom moldedsection 18, one of which is to have one or more pegs, posts orsnaps 24 that fit intoholes 20. The neonatal calorimetriccarbon dioxide detector 10 is preferably made from a transparent or translucent material, making thecalorimetric membrane 16 is visible from outside through a surface of the neonatal calorimetriccarbon dioxide detector 10. - Referring to
FIG. 3 , a plan view of the neonatal calorimetriccarbon dioxide detector 10 is shown before assembly. Shown, is the relationship of the top moldedsection 14 and the bottom moldedsection 18 with thecalorimetric membrane 16 positioned to be held between the top moldedsection 14 and the bottom moldedsection 18. There are many ways known to join the top moldedsection 14 and the bottom moldedsection 18, one of which is to have one or more pegs, posts orsnaps 24 that fit intoholes 20, thereby holding the top moldedsection 14 and the bottom moldedsection 18 together with or without an adhesive. Other methods include the use of adhesives, ultrasonic welding, etc. - Referring to
FIG. 4 , a plan view of the present invention after assembly is shown. Once the top moldedsection 14 and the bottom moldedsection 18 of the neonatal calorimetriccarbon dioxide detector 10 are assembled around thecalorimetric membrane 16, the total internal air volume is approximately 3.8 mL or less than 3.8 mL. Insertion of the neonatal calorimetriccarbon dioxide detector 10 into an airway circuit increases the total internal air volume 45 (seeFIG. 5 ) by approximately 1 mL and preferably by less than 1 mL. - Referring to
FIG. 5 , a cross-sectional view of the present invention after assembly is shown. The neonatal calorimetric carbon dioxide detector top moldedsection 14 interfaces to respiration equipment through, for example, agas tube 60. The bottom moldedsection 18 interfaces to the patient through, for example, a tracheal or endo-tracheal tube 50. The total internal air volume is approximately 3.8 mL or less than 3.8 mL. Insertion of the neonatal calorimetriccarbon dioxide detector 10 into an airway circuit increases the totalinternal air volume 45 by approximately 1 mL and preferably by less than 1 mL. - Equivalent elements can be substituted for the ones set forth above such that they perform in substantially the same manner in substantially the same way for achieving substantially the same result.
- It is believed that the system and method of the present invention and many of its attendant advantages will be understood by the foregoing description. It is also believed that it will be apparent that various changes may be made in the form, construction and arrangement of the components thereof without departing from the scope and spirit of the invention or without sacrificing all of its material advantages. The form herein before described being merely exemplary and explanatory embodiment thereof. It is the intention of the following claims to encompass and include such changes.
Claims (16)
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US12/472,011 US8256414B2 (en) | 2009-05-26 | 2009-05-26 | Neonatal colorimetric carbon dioxide detector |
US13/566,123 US8402964B2 (en) | 2009-05-26 | 2012-08-03 | Neonatal colorimetric carbon dioxide detector |
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US12/472,011 US8256414B2 (en) | 2009-05-26 | 2009-05-26 | Neonatal colorimetric carbon dioxide detector |
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US13/566,123 Continuation US8402964B2 (en) | 2009-05-26 | 2012-08-03 | Neonatal colorimetric carbon dioxide detector |
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US8256414B2 US8256414B2 (en) | 2012-09-04 |
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US13/566,123 Active US8402964B2 (en) | 2009-05-26 | 2012-08-03 | Neonatal colorimetric carbon dioxide detector |
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Cited By (5)
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---|---|---|---|---|
WO2012030232A1 (en) * | 2010-09-03 | 2012-03-08 | Fisher & Paykel Healthcare Limited | Breath indicator |
US20160025249A1 (en) * | 2014-07-22 | 2016-01-28 | Oridion Medical 1987 Ltd. | Connector with mating plate |
US10393666B2 (en) | 2012-03-12 | 2019-08-27 | Respirion, LLC | Methods, devices, systems, and compositions for detecting gases |
WO2020012465A1 (en) * | 2018-07-11 | 2020-01-16 | Oridion Medical 1987 Ltd. | Indicator lights for capnography systems |
US11324954B2 (en) | 2019-06-28 | 2022-05-10 | Covidien Lp | Achieving smooth breathing by modified bilateral phrenic nerve pacing |
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US9170193B2 (en) | 2013-06-06 | 2015-10-27 | General Electric Company | Detecting coolant leaks in turbine generators |
CA2914825C (en) | 2013-07-16 | 2022-10-18 | Palo Alto Health Sciences, Inc. | Methods and systems for quantitative colorimetric capnometry |
US9097657B2 (en) | 2013-07-23 | 2015-08-04 | General Electric Company | Leak detection of stator liquid cooling system |
Citations (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4205043A (en) * | 1978-05-04 | 1980-05-27 | Esch Victor H | Hazardous atmosphere badge |
US4211239A (en) * | 1978-05-03 | 1980-07-08 | University Of Utah | Neonatal oxygen consumption monitor |
US4879999A (en) * | 1986-03-26 | 1989-11-14 | Board Of Regents, The University Of Texas System | Device for the determination of proper endotracheal tube placement |
US5005572A (en) * | 1988-02-26 | 1991-04-09 | Brigham & Women's Hospital | CO2 indicator and the use thereof to evaluate placement of tracheal tubes |
US5197464A (en) * | 1988-02-26 | 1993-03-30 | Babb Albert L | Carbon dioxide detection |
US5273029A (en) * | 1992-04-30 | 1993-12-28 | Wilk Peter J | Endotracheal tube assembly and related method and obturator |
US5375592A (en) * | 1993-04-08 | 1994-12-27 | Kirk; Gilbert M. | Carbon dioxide detector and shield |
US5468451A (en) * | 1992-06-29 | 1995-11-21 | Minco Ab | Device for indicating the presence of carbon dioxide in a patient's exhaled air |
US5765550A (en) * | 1995-10-04 | 1998-06-16 | Siemens Elema Ab | Device for fixing and sealing a CO2 absorber container and a cover which permits rapid detachment and reaffixing |
US5846836A (en) * | 1990-06-06 | 1998-12-08 | Southwest Research Institute | Reversible detector for gaseous carbon dioxide |
US5965061A (en) * | 1995-02-03 | 1999-10-12 | Icor Ab | Method of increasing the shelf life of a colorimetric device for indicating carbon dioxide and package containing such device |
US6144869A (en) * | 1998-05-13 | 2000-11-07 | Cygnus, Inc. | Monitoring of physiological analytes |
US6187596B1 (en) * | 1997-07-11 | 2001-02-13 | Donaldson Company, Inc. | Airborne contaminant indicator |
US6378522B1 (en) * | 1998-09-02 | 2002-04-30 | Smiths Industries Public Limited | Respiration assemblies and indicators |
US6502573B1 (en) * | 2001-11-15 | 2003-01-07 | Mercury Enterprises, Inc. | Portable single patient use carbon dioxide detector |
US20100310425A1 (en) * | 2009-06-05 | 2010-12-09 | Piper Medical, Inc. | Real-time indicator detector |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
MX2011005753A (en) * | 2008-12-03 | 2011-11-18 | Illumination Man Solutions Inc | Led replacement lamp. |
-
2009
- 2009-05-26 US US12/472,011 patent/US8256414B2/en active Active
-
2012
- 2012-08-03 US US13/566,123 patent/US8402964B2/en active Active
Patent Citations (18)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4211239A (en) * | 1978-05-03 | 1980-07-08 | University Of Utah | Neonatal oxygen consumption monitor |
US4205043A (en) * | 1978-05-04 | 1980-05-27 | Esch Victor H | Hazardous atmosphere badge |
US4879999B1 (en) * | 1986-03-26 | 1996-02-06 | Nellcor Inc | Device for the determination of proper endotracheal tube placement |
US4879999A (en) * | 1986-03-26 | 1989-11-14 | Board Of Regents, The University Of Texas System | Device for the determination of proper endotracheal tube placement |
US5005572A (en) * | 1988-02-26 | 1991-04-09 | Brigham & Women's Hospital | CO2 indicator and the use thereof to evaluate placement of tracheal tubes |
US5197464A (en) * | 1988-02-26 | 1993-03-30 | Babb Albert L | Carbon dioxide detection |
US5291879A (en) * | 1988-02-26 | 1994-03-08 | Babb Albert L | Carbon dioxide detection (II) |
US5846836A (en) * | 1990-06-06 | 1998-12-08 | Southwest Research Institute | Reversible detector for gaseous carbon dioxide |
US5273029A (en) * | 1992-04-30 | 1993-12-28 | Wilk Peter J | Endotracheal tube assembly and related method and obturator |
US5468451A (en) * | 1992-06-29 | 1995-11-21 | Minco Ab | Device for indicating the presence of carbon dioxide in a patient's exhaled air |
US5375592A (en) * | 1993-04-08 | 1994-12-27 | Kirk; Gilbert M. | Carbon dioxide detector and shield |
US5965061A (en) * | 1995-02-03 | 1999-10-12 | Icor Ab | Method of increasing the shelf life of a colorimetric device for indicating carbon dioxide and package containing such device |
US5765550A (en) * | 1995-10-04 | 1998-06-16 | Siemens Elema Ab | Device for fixing and sealing a CO2 absorber container and a cover which permits rapid detachment and reaffixing |
US6187596B1 (en) * | 1997-07-11 | 2001-02-13 | Donaldson Company, Inc. | Airborne contaminant indicator |
US6144869A (en) * | 1998-05-13 | 2000-11-07 | Cygnus, Inc. | Monitoring of physiological analytes |
US6378522B1 (en) * | 1998-09-02 | 2002-04-30 | Smiths Industries Public Limited | Respiration assemblies and indicators |
US6502573B1 (en) * | 2001-11-15 | 2003-01-07 | Mercury Enterprises, Inc. | Portable single patient use carbon dioxide detector |
US20100310425A1 (en) * | 2009-06-05 | 2010-12-09 | Piper Medical, Inc. | Real-time indicator detector |
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US8402964B2 (en) | 2013-03-26 |
US20120296229A1 (en) | 2012-11-22 |
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